Tumor and normal tissue response to interstitial photodynamic therapy of the rat R-1 rhabdomyosarcoma

Interstitial photodynamic laser therapy in interventional oncology

Photodynamic therapy (PDT) is a well-investigated locoregional cancer treatment in which a systemically administered photosensitizer is activated locally by illuminating the diseased tissue with light of a suitable wavelength. PDT offers various treatment strategies in oncology, especially palliative ones. This article focuses on the development and evaluation of interstitial PDT for the treatment of solid tumors, particularly liver tumors. The PDT is mostly used for superficial and endoluminal lesions like skin or bladder malignancies and also more frequently applied for the treatment of lung, esophageal, and head and neck cancer. With the help of specially designed application systems, PDT is now becoming a practicable option for solid lesions, including those in parenchymal organs such as the liver. After intravenous treatment with the photosensitizer followed by interstitial light activation, contrast-enhanced computed tomography shows the development of therapy-induced necrosis around the light-guiding device. With the use of multiple devices, ablation of liver tumors seems to be possible, and no severe side effects or toxicities related to the treatment are reported. PDT can become a clinically relevant adjunct in the locoregional therapy strategies.

Evaluation of the photosensitizer Tookad for photodynamic therapy on the Syrian golden hamster cheek pouch model: light dose, drug dose and drug-light interval effects

We have evaluated the efficacy of the new photosensitizer (PS) Tookad in photodynamic therapy (PDT) in vivo. This PS is a palladium-bacteriopheophorbide presenting absorption peaks at 762 and 538 nm. The light dose, drug dose and drug injection-light irradiation interval (DLI), ranging between 100 and 300 J/cm2, 1 and 5 mg/kg and from 10 to 240 min, respectively, were varied, and the response to PDT was analyzed by staging the macroscopic response and by the histological examination of the sections of the irradiated cheek pouch. The level of PDT response, macroscopically and histologically, shows a strong dependence on the DLI, light dose and drug dose at the applied conditions in the normal hamster cheek pouch. A decay of the tissular response with increasing DLI is observed corresponding to a time of half-maximum response ranging from 10 to 120 min, depending on drug dose and light dose. The tissues affected at the lowest doses are predominantly the vascularized diffuse connective tissue situated between the inner and outer striated muscle (SM) layers as well as these muscle layers themselves. The highest response at the shortest DLI and the absence of a measurable response at DLI longer than 240 min at 300 J/cm2 and drug dose of 5 mg/kg are characteristics of a predominantly vascular effect of this PS. This observation suggests that Tookad could be effective in PDT of vascularized lesions or pathologies associated with the proliferation of neovessels.

Performance of isotropic light dosimetry probes based on scattering bulbs in turbid media

In a previous paper the calibration of an isotropic light detector in clear media was described and validated. However, in most applications the detector is used to measure light distribution in turbid (scattering) media, that is, in tissues or tissue equivalent optical phantoms. Despite its small diameter (typically 0.8 mm), inserting the detector in a turbid medium may perturb the light distribution and change the fluence rate at the point of measurement. In the present paper we estimate the error in the fluence rate measured by a detector in turbid media after calibration in a clear medium (air), using an optical phantom and detector bulbs of different optical properties. The experimental results are compared with calculations using the diffusion approximation to the transport equation in a spherical geometry. From measurements in optical phantoms and the results of the calculations it appears that introduction of the detector into a water-based turbid medium with refractive index, absorption- and scattering coefficients different from those of the detector bulb may require corrections to the detector response of up to 10-15%, in order to obtain the true fluence rate in that medium. The diffusion model is used to explore the detector response in a number of tissues of interest in photodynamic therapy, using tissue optical properties from the literature. Based on these model calculations it is estimated that in real tissues the fluence rate measured by the detector is up to 3% below the true value.

Feasibility study of a system for combined light dosimetry and interstitial photodynamic treatment of massive tumors

A system for the photodynamic laser treatment of massive tumors that employs multiple optical fibers to be inserted into the tumor mass is described. The light flux through the tumor can be assessed by use of the individual fibers both as transmitters and as receivers. With a computer model that describes the diffusive light propagation, optical dosimetry is under development. The system has been tested in an experimental animal tumor model in preparation for clinical work. Currently, delta-aminolevulinic acid is used as a sensitizer, activated by 635-nm radiation from a 2.0-W compact diode laser system. With the availability of future, highly selective drugs absorbing approximately 750 nm, larger tumor volumes should be treatable, and surrounding, sensitive normal tissue should be spared.

An interstitial light assembly for photodynamic therapy in prostatic carcinoma

OBJECTIVE

To develop an interstitial laser light delivery system using multiple optical fibres for photodynamic therapy (PDT) in the treatment of prostate cancer.

PATIENTS AND METHODS

A laser beam was divided equally with a 1 x 4 fibre splitter to deliver PDT simultaneously through four 2-cm long, flexible cylindrical optical diffusers. Biplanar transrectal ultrasonography (TRUS) and a template were used to position the optical fibres percutaneously. In vivo measurements of light penetration depth (1/micro[eff] ) in prostate tissue were made in seven patients, using a sheathed isoprobe to measure light fluence rates at varying radial distances from the diffuser. The prostate was fixed with stabilization needles to minimize displacement during needle placement.

RESULTS

The mean (sd, range) micro(eff) in the prostates of the seven patients was 0.35 (0.07, 0.22-0.44) mm-1, which produced closely parallel slopes of light attenuation. However, there was up to a 10-fold variation in absolute light levels at the same diffuser-detector separation distances amongst the seven patients, probably caused by blood pooling around the diffuser light source. A similar problem around the isoprobe detector was overcome by sheathing the probe in clear plastic tubing. By stabilizing the prostate, the optical fibre positioning was precise to within 2 mm.

CONCLUSION

Although this light delivery and TRUS assembly were developed for clinical PDT in the prostate, the same instrumentation can be used reliably for in vivo light-penetration studies. Haemorrhage was unpredictable and highlighted one of the main problems which needs to be overcome.

Effective treatment of liver metastases with photodynamic therapy, using the second-generation photosensitizer meta-tetra(hydroxyphenyl)chlorin (mTHPC), in a rat model

The only curative treatment for patients with liver metastases to date is surgery, but few patients are suitable candidates for hepatic resection. The majority of patients will have to rely on other treatment modalities for palliation. Photodynamic therapy (PDT) could be a selective, minimally invasive treatment for patients with liver metastases. We studied PDT in an implanted colon carcinoma in the liver of Wag/Rij rats, using the photosensitizer meta-tetra(hydroxyphenyl)chlorin (mTHPC). mTHPC tissue kinetics were studied using ex vivo extractions and in vivo fluorescence measurements. Both methods showed that mTHPC kinetics were different for liver and tumour tissue. After initial high levels at 4 h after administration (0.1 and 0.3 mg kg(-1)) mTHPC in liver tissue decreased rapidly in time. In tumour tissue no decrease in photosensitizer levels occurred, with mTHPC remaining high up to 48 h after administration. Both concentration data and fluorescence data showed an increase in tumour to liver ratios of up to 6.3 and 5.0 respectively. Illumination with 652 nm (15 J) resulted in extensive damage to tumour tissue, with necrosis of up to 13 mm in diameter. Damage to normal liver tissue was mild and transient as serum aspartate aminotransferase and alanine aminotransferase levels normalized within a week after PDT treatment. Long-term effects of mTHPC-PDT were studied on day 28 after treatment. Regardless of drug dose and drug-light interval, PDT with mTHPC resulted in complete tumour remission in 27 out of 31 treated animals (87%), with only four animals in which tumour regrowth was observed. Non-responding tumours proved to be significantly larger (P < 0.001) in size before PDT treatment. This study demonstrates that mTHPC is retained in an intrahepatic tumour and that mTHPC-PDT is capable of inducing complete tumour remission of liver tumours.

What does photodynamic therapy have to offer radiation oncologists (or their cancer patients)?

Major advances have recently been made in photodynamic therapy (PDT) for clinical application, including the development of more powerful photosensitizers and light sources and suitable light applicators. PDT is emerging as an attractive new form of cancer therapy, suitable for treating superficial lesions (less than 1 cm in depth) and carcinoma in situ, or as an adjuvant to surgery for more bulky disease. PDT is therefore complementary to radiotherapy which is better suited to treating larger tumours. There are some qualitative similarities between light distribution in tissue during superficial illumination and ionizing radiation dose distributions during external beam irradiation, or between interstitial PDT and brachytherapy, although the geometric scale is very different (visible light penetrates a maximum of 5-10 mm in tissue). The contribution of scattered light to tissue irradiance is much greater than for ionizing radiation and in situ light dosimetry is very important (although rather complicated) to ensure adequate illumination without over-treating. Dosimetry and treatment planning are highly advanced for ionizing radiation and are routine in all radiotherapy departments. Proper in situ light dosimetry and dose distribution calculation for PDT is in its infancy. Physicists have an important role to play in the further optimization of clinical PDT and much of the infrastructure and expertise present in the radiotherapy department is ideally suited to accommodate PDT. In this review, parallels and contrasts are made between PDT and ionizing radiation for both mechanistic and dosimetric aspects of the therapies. A summary of the most interesting clinical applications is also given.

Interstitial photodynamic therapy with tetra(m-hydroxyphenyl)chlorin: tumor versus striated muscle damage

PURPOSE

The present study was initiated to determine the conditions under which a single photodynamic treatment would induce maximal damage to a tumor with no or at least minimal reversible damage to a normal striated muscle.

METHODS AND MATERIALS

The technique of interstitial light delivery was used after prior 0.5 mg/kg tetra(m-hydroxyphenyl)chlorin administration in a hamster model. After having estimated the threshold light doses required for minimal muscle damage, the same light doses were applied to squamous cell carcinomas to evaluate the efficiency of interstitial photodynamic therapy. Sixteen and 96 h after the injection, irradiation at 650 nm was performed on the thigh muscle of the left hind leg. The applied light doses ranged between 0.3-15 J and were delivered at an intensity of 44 mW per cm of diffuser length.

RESULTS

The threshold of muscle damage was obtained using light doses of 1.5-3 J at two drug-light intervals of 16 and 96 h, respectively. More than 85% of the tumor mass was destroyed when lesions were illuminated using these threshold conditions. In terms of immediate short-term tumor response, this means that for the given irradiation conditions, a relatively low threshold energy of only 1.5 or 3 J, depending on the drug-light interval, is sufficient to induce massive tumor destruction with minimal muscle damage.

CONCLUSION

These results have implications for evaluating interstitial PDT for squamous cell cancers in unfavorable localization in the oral cavity or pharynx, such as at the base of the tongue.

Interstitial photodynamic therapy with the second-generation photosensitizer bacteriochlorin a in a rat model for liver metastases

Bacteriochlorin a (BCA) is a second-generation photosensitizer that is effective in tumour destruction upon illumination with light of a wavelength of 760 nm. Tissue penetration by light at this wavelength is greater compared with wavelengths at which commonly used photosensitizers are illuminated, making it possible to treat larger tumours. In a model of experimental liver metastases in rats, we measured lesion sizes after interstitial illumination of tumours at different times after intravenous administration of BCA (10 mg kg(-1) bodyweight), as well as BCA concentrations in liver and tumour tissue. In both, BCA concentrations showed a rapid decline within the first 4 h, followed by a slow decrease over the next 20 h, suggesting biphasic pharmacokinetics. No selective uptake in tumour tissue was observed. A near-linear relationship was found between lesion sizes and liver and tumour BCA concentrations, suggesting that optimal results with photodynamic therapy (PDT) could be obtained by illumination within a short time interval after administration, when tissue concentrations are highest. No severe liver toxicity was observed as indicated by serum ALAT levels. However, in all tumours evaluated, islands of vital-looking cells were present leading to tumour regrowth within 35 days. In view of the obtained lesion diameters of approximately 13 mm after BCA-PDT and the rapid clearance rate of BCA, the concept of a near-infrared absorbing photosensitizer for PDT of liver tumours is a potential interesting strategy.

Light dosimetry in vivo

This paper starts with definitions of radiance, fluence (rate) and other quantities that are important with regard to in vivo light dosimetry. The light distribution in mammalian tissues can be estimated from model calculations using measured optical properties or from direct measurements of fluence rate using a suitable detector. A historical introduction is therefore followed by a brief discussion of tissue optical properties and of calculations using diffusion theory, the P3-approximation or Monte Carlo simulations. In particular the form of the scattering function is considered in relation to the fluence rate close to the tissue boundary, where light is incident. Non-invasive measurements of optical properties yield the absorption coefficient mu a and mu s(1 - g), where mu s is the scattering coefficient and g is the mean cosine of the scattering angle. An important question is whether this combination is sufficient, or whether g itself must be known. It appears that for strongly forward scattering, as in mammalian tissues, rather detailed knowledge of the scattering function is needed to reliably calculate the fluence rate close to the surface. Deeper in the tissue mu s (1 - g) is sufficient. The construction, calibration and use of fibre-optic probes for measurements of fluence rate in tissues or optical phantoms is discussed. At present, minimally invasive absolute fluence (rate) measurements seem to be possible with an accuracy of 10-20%. Examples are given of in vivo measurements in animal experiments and in humans during clinical treatments. Measurements in mammalian tissues, plant leaves and marine sediments are compared and similarities and differences pointed out. Most in vivo light fluence rate measurements have been concerned with photodynamic therapy (PDT): Optical properties of the same normal tissue may differ between patients. Tumours of the same histological type may even show different optical properties in a single patient. Treatment-induced changes of optical properties may also occur. Scattered light appears to contribute substantially to the light dose. All these phenomena emphasize the importance of in situ light measurements. Another important dosimetric parameter in PDT is the concentration and distribution of the photosensitizer. Apart from in vivo fluorescence monitoring, the photosensitizer part of in vivo PDT dosimetry is still in its infancy.

Photodynamic therapy of oral cancer. A review of basic mechanisms and clinical applications

Photodynamic therapy (PDT) is an experimental cancer treatment modality. PDT is based on the accumulation of a photosensitive dye in premalignant and malignant lesions. A certain period of time after the dye has been administered, tumor tissue may contain more of the sensitizer then the surrounding normal tissues. When tissue containing the sensitizer is exposed to light of a proper wavelength and dose, a photochemical reaction between sensitizer and light will occur. The activated photosensitizer reacts with available oxygen which subsequently damages cells and eventually may cause necrosis of the tumor. Photosensitizers can also be used for fluorescence detection. If a tumor contains more of the photosensitizer than the surrounding normal tissue, its fluorescence can potentially be utilized to detect tumors. Analogous to PDT, this can therefore be referred to as photodynamic detection (PDD). This paper reviews the basic mechanisms and clinical applications of PDT and PDD. Emphasis is placed on PDD and PDT with the photosensitizer Photofrin for detection and treatment of premalignant epithelial lesions and squamous cell carcinomas of the oral mucosa.

In situ comparison of 665 nm and 633 nm wavelength light penetration in the human prostate gland

The depth of treatment in photodynamic therapy (PDT) of tumors varies with the wavelength of light activating the photosensitizer. New generation photosensitizers that are excited at longer wavelengths have the potential for increasing treatment depths. Tin ethyl etiopurpurin (SnET2), a promising second-generation photosensitizer is maximally activated at 665 nm, which may be significantly more penetrating than 633 nm light currently used with porphyrins in PDT. The penetration of 665 nm and 633 nm wavelength red light in the prostate gland was compared in 11 patients undergoing prostatic biopsies for suspected prostatic cancer. Interstitial optical fibers determined the light attenuation within the prostate gland. Of the 11 patients, 7 had dual wavelength and 4 had single wavelength studies. The mean attenuation coefficients, mueff, for 665 nm and 633 nm wavelength light were 0.32 +/- 0.05 mm-1 and 0.39 +/- 0.05 mm-1, respectively, showing a statistically significant difference (P = 0.0003). This represented a 22% increase in the mean penetration depth and at 10 mm from the delivery fiber there was 1.8 times as much 665 nm light fluence than 633 nm. The mean mueff at 665 nm for benign and malignant prostate tissue were similar (P = 0.42), however, there was significant interpatient variation (mueff ranging from 0.24 to 0.42 mm-1) reflecting biological differences of therapeutic importance. The enhanced light fluence and penetration depth with 665 nm light should allow significantly larger volumes of prostatic tissue to be treated with SnET2-mediated PDT.

In vivo laser light distribution in human prostatic carcinoma

The extent of laser light diffusion within prostatic tumor is of major importance in the treatment of localized prostatic cancer with photodynamic therapy (PDT). The penetration of 633 nm. wavelength red light was studied in eleven patients with suspected prostatic cancer using a novel method suitable for in situ measurements. Light delivery and detector fiber, placed interstitially within the gland, determined light attenuation at different interfiber separations. Of 11 patients, 10 had bilateral and 1 had single lobe studies. The mean +/- the standard error of the mean attenuation coefficients (sigma eff) for benign and malignant prostate tissue were 0.35 +/- 0.02 mm-1 and 0.36 +/- 0.02 mm-1, respectively, indicating similar optical densities (p = .58). Patients with bilateral lobe involvement showed little intraglandular variation in sigma eff (p = 0.23). However, there was interpatient variation (sigma eff = 0.28 to 0.48 mm-1) reflecting biological differences which, though therapeutically important, were not statistically significant (p = 0.057). This study showed that treatment requires individualization and predicted that 4 cylindrical diffusers are expected to destroy 25 ml. of prostatic tumor with PDT.

Interaction of the bioreductive drug SR 4233 and photodynamic therapy using photofrin in a mouse tumor model

PURPOSE

Combining the bioreductive drug SR 4233 with interstitial photodynamic therapy to improve efficacy.

METHODS AND MATERIALS

RIF1 tumors were implanted subcutaneously in mice and treated with interstitial photodynamic therapy. The bioreductive drug SR 4233 (a benzotriazine which exhibits preferential cell killing under hypoxic conditions) was combined with photodynamic therapy to exploit the induced hypoxia. SR 4233 was given to mice prior to or just after illumination. The effect of multiple SR 4233 injections given over the first 3 days after treatment was also evaluated.

RESULTS

The results from experiments with a 24 hr interval between Photofrin and illumination showed that SR 4233 produced only a small additional growth delay compared with photodynamic therapy alone (light doses of 300 or 400 J/cm, combined with 6 x 15 mg/kg SR 4233). Some cures (6/60), however, were found in groups treated with 200 to 400 J/cm with SR 4233, whereas only two cures (2/77) occurred at light doses up to 400 J/cm after photodynamic therapy alone. Reducing the interval between Photofrin injection and illumination increased the number of cures in the combination group, although this was associated with a marked increase in toxicity. A small increase in cure rate was observed for the combination of photodynamic therapy (6 hr interval) and SR 4233, although this was not significant due to the limited number of mice that survived treatment.

CONCLUSION

Only a limited effect of combining SR 4233 and interstitial photodynamic therapy was observed in this tumor model. A possible explanation could be the rapid conversion of SR 4233 into inactive metabolites.

Optimization of multifiber light delivery for the photodynamic therapy of localized prostate cancer

The understanding of light distribution within the target organ is essential in ensuring efficacy and safety in photodynamic therapy (PDT). A computer simulator of light distribution in prostatic tissue was employed for optimizing dosimetry for PDT in localized prostatic cancer. The program was based on empirically determined light distributions and optical constants and an assumed fluence rate differential from fiber source to necrosis periphery. The diffusion theory approximation to the Boltzmann transport equation was the applicable formulation relevant to prostatic tissue, which has a high albedo with forward-scattering characteristics. Solving this equation of diffusive transfer for the appropriate fiber geometry yielded the energy fluence distributions for cleaved fiber and cylindrical diffuser light delivery. These distributions, confirmed by our measurements, show a 1/r and 1/square root of r dependency (r = distance from light source) of the fluence phi (r) for the cleaved fiber and diffuser, respectively. This manifests itself by the tighter spacing of energy fluence isodoses in the case of the cleaved fiber. It was predicted that for a typical PDT regime a single interstitially placed cleaved fiber would treat 0.05-0.72 cm3. Four parallel fibers improved the uniformity of light distribution and treatment volume, and an interfiber separation of 12 mm would be necessary to provide optimal overlap of PDT necrosis, treating 0.26-3.6 cm3. The cylindrical diffuser, however, could treat larger volumes, and it was predicted that four 3 cm long diffusers at an optimal separation of 25 mm would treat 25-88 cm3 of prostatic tissue.

Pilot study on light dosimetry for endobronchial photodynamic therapy

Endobronchial photodynamic therapy (EB-PDT) using photofrin as the photosensitizer is currently being evaluated as a new treatment modality for inoperable endobronchial tumors. One of the current problems with EB-PDT is the lack of adequate light dosimetry, which hampers proper interpretation of treatment results. In this study exploratory light dosimetry experiments were performed in plastic bronchus models using either a microlens-tipped fiber (suitable for illumination of small superficial tumors) or a cylindrical diffuser fiber (suitable for intraluminal illumination or interstitial illumination of partially obstructing tumors). It is shown that the light fluence prescriptions of current clinical protocols yield a different fluence in tissue for each illumination modality. Depending on the actual placement of the cylindrical diffuser within the lumen, the light fluence at 5 mm depth in the homogeneous tissue model may vary by a factor of 3. The results were confirmed by in vivo experiments in the trachea of a pig. There is a possibility of enhanced tissue response by accidental hyperthermia induced during EB-PDT. The temperature rise was therefore estimated in vivo using a rat tumor model to mimic clinical EB-PDT. Temperature rises of at least 5 degrees C and 10 degrees C can be expected for intraluminal and intratumoral illumination, respectively, at 3.5 +/- 1 mm depth in tissue and 400 mW/cm diffuser output. Light fluence and its distribution in the bronchus strongly depend on the geometry and the optical properties of the tissue as well as on the technique of illumination. As a result of inadequate dosimetry, significant variations in treatment response between patients may be expected.